|Publication number||US6937016 B2|
|Application number||US 10/153,580|
|Publication date||Aug 30, 2005|
|Filing date||May 22, 2002|
|Priority date||May 22, 2001|
|Also published as||DE10125233C1, US20020196021|
|Publication number||10153580, 153580, US 6937016 B2, US 6937016B2, US-B2-6937016, US6937016 B2, US6937016B2|
|Original Assignee||Siemens Aktiengesellschaft|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (19), Referenced by (1), Classifications (4), Legal Events (3)|
|External Links: USPTO, USPTO Assignment, Espacenet|
1. Field of the Invention
The present invention is directed to a reception device for detecting an electromagnetic radio-frequency wave emitted by the examination subject of a nuclear magnetic resonance tomography installation, of the type having a first reception coil, a first amplifier allocated to the first reception coil, a second reception coil whose reception signal is phase-shifted with respect to the reception signal of the first reception coil, particularly by a phase angle of 90°, comprising a second amplifier allocated to the second reception coil, and a common signal line via which the output signals of the two amplifiers are carried off.
2. Description of the Prior Art
For receiving the circularly polarized radio-frequency signal, two orthogonal polarization components are separately received in a magnetic resonance tomography installation. In, for example, a vertical field apparatus, a first polarization component is received parallel to the patient axis and a second polarization component is received perpendicular to the patient axis. For receiving the first polarization component parallel to the patient axis, a loop coil can be used that surrounds the entire patient body or an extremity to be examined. For the reception of the second polarization component, for example, a butterfly coil or saddle coil is used. Both field components of the circularly polarized magnetic field part of the electromagnetic radio-frequency signal can be detected with the separately existing reception coils or reception antennas.
The reception signals of the separately existing reception antennas are amplified in separate pre-amplifiers allocated to the reception antennas and are supplied via a 90° coupler (90° combiner) that takes the phase shift between the two polarization components into consideration to a common signal line. Via the common signal line, the radio-frequency signals combined in this way are supplied to the image evaluation, image reconstruction and image display. The phase shift between the two polarization components typically amounts to 90°. However, dependent on the structure of the magnetic resonance tomography installation, other values below this and above this are possible.
The combiner is composed of a capacitive impedance and of an inductive impedance. The output impedance of the combiner must be matched to the impedance of the common signal line. The lines leading to the combiner as well as the combiner itself must be shielded in an involved way. The known combiner also has the disadvantage that it requires a certain spatial volume for the circuitry, leading to unergonomically bulky arrangements, particularly in the manufacture of non-stationary, i.e. portable coil arrangements, for example in the manufacture of surface coils, because the combiner must be accommodated on the coil arrangement.
An object of the present invention is to provide a reception device for a magnetic resonance tomography installation wherein the aforementioned disadvantages are avoided.
This object is achieved in a reception device of the type initially described, wherein at least one of the amplifiers compensates the phase shift between the two reception signals.
The invention is based on the perception that the function of the previously employed combiner and be at least partially displaced into the amplifiers or pre-amplifiers, and the combiner can thus be partially or entirely eliminated.
The invention achieves the advantage that the reception device can be constructed more simply, smaller, more economically, less susceptible to malfunction and in a more space-saving way. Moreover, fewer adjustment tasks are needed for the impedance matching, so that the manufacturer is also simplified and the testing costs are reduced. The amplifiers and pre-amplifiers, for example, can have a separate or a common shielding housing wherein the function of the previously employed combiner is relocated.
The output impedances of the two amplifiers are preferably established between the two reception signals for compensating the phase shift.
In particular, a coil at the output side or a capacitor at the output side is used for this purpose.
For processing the reception signals that may be of different strength under certain circumstances, it can be necessary to weight these differently. To this end, for example, the gains of the allocated amplifiers can be set differently by connecting active components. Alternatively or additionally, a weighting is undertaken by a suitable setting of the output impedances, particularly of the coil present at the output side and/or of the capacitor present at the output side. It is not only a phase angle but also an amount, namely that can be set via the output impedance. The case of identical weighting by the output impedances, i.e. the case of equal amounts, is referred to below as the “symmetrical case”.
In a preferred embodiment, the output impedances of the two amplifiers are fashioned for generating mutually opposite phase angles, particularly for generating phase angles of −45° or +45°. In this embodiment, the amplifiers contribute in a way that is the same in magnitude but oppositely directed to generating the desired phase shift. This is preferably true in the “symmetrical case”. Otherwise, the phase angles can have the same operational sign under certain circumstances, but the difference is adapted to the phase shift between the reception signals that is to be balanced.
It is expedient for avoiding reflections at the output of the two amplifiers for the output impedances of the two amplifiers to be additionally directed to the impedance of the common signal line for adaptation. In complex notation, this means that the output impedances of the two amplifiers comprise complex values that accomplish the generation of a phase shift as well as matching to the signal line.
Preferably, the output impedances of the two amplifiers—in complex notation—are complex conjugates (of each other), particularly in the symmetrical case.
For example, the output impedance of one of the two amplifiers—in complex notation—exhibits the value X+i·X, and the output impedance of the other amplifier exhibits the value X−i·X, whereby X indicates the desired impedance of the common signal line and preferably exhibits a value of 50 Ω. This is preferably true in the symmetrical case.
As already mentioned, it is advantageous in the reception device of the invention that a separate combiner as well as an element for impedance matching of the pre-amplifiers to the common signal line can be eliminated. Preferably, the output lines of the two amplifiers are therefore connected to the common signal line either directly, or without interposition of phase-delaying elements, particularly without longer signal paths or lines that produce noticeable phase shifts.
Due to the susceptibility to malfunction and shielding, it is expedient for the two amplifiers to be fashioned as an assembly unit and, in particular, to be arranged in a common housing or shielded housing.
For easier comprehension, a phase shift of exactly 90° between the received polarization components forms the basis of the discussion below. The considerations can be transferred to cases having a different phase shift.
The output signals of the two amplifiers 15, 17—respectively shielded with separate housings—are supplied to a 90° combiner 25 via shielded coaxial lines 21 and 23 in the known reception device 1 of FIG. 1. The 90° combiner 25 has to be separately shielded. At its output, the 90° combiner 25 is in communication with a common signal line 19 implemented as a shielded coaxial cable and via which the signals are supplied in common to the image evaluation, circuitry and other components.
The circuit structure of the two amplifiers 15, 17 is only schematically shown, without detail. The circuit includes a field effect transistor and a transistor at the output side. For matching the output impedance Z2,0 of the first amplifier 15 to an ohmic line impedance of R0=50 Ω of the line 21, the amplifier 15 contains a capacitor C2,0 connected in parallel, and an inductance L2,0 connected in series, at its output. For matching the output impedance Z1,0 of the second amplifier 17 to an ohmic line impedance R0=50 Ω of the line 23, the amplifier 17 contains a capacitor C1,0 connected in parallel, and an inductance L1,0 connected in series, at its output.
Conventionally, the output impedances Z2,0 and Z1,0 of the amplifiers 15, 17 are respectively matched to a value of R0=50 Ω with the capacitors C1,0 C2,0 and coils L1,0, L2,0. The output resistance R of the transistor must be taken into consideration. The following matching condition derives:
The above matching condition is reproduced for the first amplifier 15 and analogously applies to the second amplifier 17 with the values C1,0, L1,0. the radian frequency ω=2·π·f of the magnetic tomograph (for example, 63.6 MHz for a 1.5 Tesla system). The creation of the matching condition is illustrated in detail in the equivalent circuit diagram of FIG. 2. In
The following dimensioning rules for the capacitor C2,0 derive from the matching condition according to Equation 1:
and, for the coil L2,0:
L 2,0 =R 0 ·R·C 2,0=781.4 nH Equation 3
The combiner 25 shown in
In order to realize a 90° combiner, the impedances ZC=−i 50 Ω and ZL=+i 50 Ω must apply given a source impedances Z1,0=Z2,0=50 Ω at the input side. The output signal is then established by:
In order to achieve an exact phase difference, the amplifier outputs are usually set to 50 Ω. Trimming capacitors T1, T2 with which the combiner 25 can also be exactly set are provided for the two impedances ZC and ZL.
The reception device 1 of the invention in
Since the two amplifiers 35, 37 of
In contrast to the known arrangement shown in
The following dimensioning rules derive therefrom for the capacitors C1, C2 and coils L1, L2 present at the output side in the amplifiers 15, 17 (only shown here for the first amplifier 15):
C2=C2,0 Equation 7
Thus, due to an increase to 906.5 nH, or a reduction (to 656.3 nH) in the values of the inductances L2, L1 compared to the corresponding values L2,0, L1,0 of the case shown in
The amplifiers 35, 37 with “quasi-integrated combiner” have the advantage that a separate combiner is not required and, thus, costs for material and testing can be eliminated. A coil module with one or both coils 3, 5 and one or both amplifiers 35 and 37 can be constructed smaller as a result. In particular, an array coil can thus be constructed in an especially simple way.
Although modifications and changes may be suggested by those skilled in the art, it is the intention of the inventor to embody within the patent warranted hereon all changes and modifications as reasonably and properly come within the scope of the inventor's contribution to the art.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US4095168 *||Feb 22, 1977||Jun 13, 1978||Varian Associates, Inc.||Rf pick-up coil circuit for a wide tuning range nuclear magnetic resonance probe|
|US4467282 *||Jul 23, 1982||Aug 21, 1984||Siemens Aktiengesellschaft||High-frequency magnet system for nuclear spin tomography|
|US4857849 *||Mar 25, 1988||Aug 15, 1989||Mitsubishi Denki Kabushiki Kaisha||High frequency magnetic field generator for nuclear magnetic resonance|
|US5170123 *||Aug 11, 1989||Dec 8, 1992||Picker International, Inc.||Magnetic resonance imager with digital transmitter/receiver|
|US5179332 *||Aug 16, 1991||Jan 12, 1993||General Electric Company||NMR radio frequency coil with disable circuit|
|US5208537 *||Nov 6, 1991||May 4, 1993||Siemens Aktiengesellschaft||Method for matching antennas in a nuclear magnetic resonance imaging apparatus|
|US5252922 *||Apr 30, 1991||Oct 12, 1993||Hewlett-Packard Company||Radiofrequency focusing of magnetic resonance images|
|US5430378 *||Feb 22, 1994||Jul 4, 1995||Board Of Regents - Univ Of Ne||NMR quadrature detection array|
|US5489848 *||Apr 5, 1995||Feb 6, 1996||Kabushiki Kaisha Toshiba||Magnetic resonance imaging apparatus|
|US5909120 *||Sep 22, 1997||Jun 1, 1999||Kabushiki Kaisha Toshiba||Gradient magnetic field electronic power supply for gradient coil|
|US6029082 *||Nov 24, 1997||Feb 22, 2000||Picker International, Inc.||Less-claustrophobic, quadrature, radio-frequency head coil for nuclear magnetic resonance|
|US6031746 *||Sep 4, 1998||Feb 29, 2000||General Electric Company||Switching amplifier for generating continuous arbitrary waveforms for magnetic resonance imaging coils|
|US6133737 *||May 18, 1998||Oct 17, 2000||Siemens Aktiengesellschaft||Circularly polarizing antenna for a magnetic resonance apparatus|
|US6177796 *||Jul 8, 1999||Jan 23, 2001||Esaote S.P.A.||Radio frequency signal receiving unit, particularly for nuclear magnetic resonance imaging machines|
|US6208135 *||Jul 22, 1994||Mar 27, 2001||Steve J. Shattil||Inductive noise cancellation circuit for electromagnetic pickups|
|US6211671 *||Nov 3, 1999||Apr 3, 2001||Genghiscomm Corporation||Interference-cancellation system for electromagnetic receivers|
|US6348791 *||Mar 29, 2001||Feb 19, 2002||Genghiscomm, L.L.C.||Method and apparatus for a full-duplex electromagnetic transceiver|
|US6351124 *||May 24, 2000||Feb 26, 2002||Siemens Aktiengesellschaft||Antenna system for the reception of magnetic resonance signals|
|US6396273 *||Feb 2, 2001||May 28, 2002||Medrad, Inc.||Magnetic resonance imaging receiver/transmitter coils|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US7466130 *||Jan 31, 2007||Dec 16, 2008||Fonar Corporation||Phased array shoulder coil|
|Aug 19, 2002||AS||Assignment|
Owner name: SIEMENS AKTIENGESELLSCHAFT, GERMANY
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:WANG, JIANMIN;REEL/FRAME:013204/0351
Effective date: 20020529
|Jan 15, 2009||FPAY||Fee payment|
Year of fee payment: 4
|Jan 11, 2013||FPAY||Fee payment|
Year of fee payment: 8